JP2003532150A - Method for improving human vision, visual device for improving human vision, and optical system for improving human vision - Google Patents

Abstract

(57) SUMMARY The present invention includes a calibration that combines high term monochromatic and chromatic aberrations. Such a calibration results in greater visual benefit than realized by calibrating only one of the high number of monochromatic or chromatic aberrations. High term monochromatic aberrations are calibrated by introducing appropriate phase shapes to compensate for wavefront aberrations of the eye (107). Compensation is provided by a contact lens (152), an intraocular lens, an ophthalmic inlay, or an ophthalmic onlay by keratoplasty with appropriate surface topography or achieved by techniques such as refractive surgery. Apodization filters are performed by providing non-uniform amplitude transmission through the pupil of the eye. Devices such as contact lenses for calibrating high term monochromatic aberrations include a suitable apodization filter for calibrating chromatic aberration. The external optical device for calibrating chromatic aberration may be combined with a contact lens for calibrating monochromatic aberration having a high number of terms.

Description

Detailed Description of the Invention

[0001]

TECHNICAL FIELD OF THE INVENTION

The present invention relates to an apparatus and method for improving visual acuity and retinal images, and more particularly to human visual acuity and retina by calibrating monochromatic aberration with high eye number and chromatic aberration with high eye number. Apparatus and method for improving images in a computer.

[0002]

[Prior art]

Despite significant advances in eyeglass and contact lens design, most ophthalmic lenses correct up to the second term (second order) ocular aberration known as defocus and astigmatism. I'm just doing it. Terms such as surface aberrations, coma, and various irregular aberrations (orders,
High order monochromatic (single wavelength range limited) ocular aberrations remain uncorrected by spectacles, contact lenses, corneal reshaping, inlays, onlays, and other current vision correction techniques. These high ocular aberrations blur the image formed on the retina that occurs in degraded vision performance, and also blur the image taken from the retina of a living human. Until recently, there is no fast and efficient device for quantitatively measuring the above-mentioned high-order irregular aberrations of the eyeball, and monochromatic (one wavelength range limited) ocular aberrations other than defocus and astigmatism are not available. There was also no practical mechanism available to calibrate.

Liang et al., "American Journal of Optical Physiology" (J. Opt. Soc. Am. A.)
, (Vol. 11, No. 7, pp. 1947 to 1957, July 1994), the Hartmann-Shack wavefront sensor used to measure the monochromatic wave aberrations of the human eye. Is disclosed. This is done by feeling the wavefront rising from the eye caused by the retinal reflection of the light beam focused on the depression on the retina. Using the system thus disclosed, its author
We were able to measure polynomial functions up to only terms. However, wavefronts suitable for polynomials up to the fourth term only do not provide a sufficient description of eye aberrations. Continuing, and demonstrating, in its entirety by reference, US Pat. No. 5,777,719 by William et al., An improvement on the wavefront sensor used by Liang et al. Measurement data and corrections for more than 5 monochromatic aberrations have been made. By using a deformed mirror that incorporates a modified wavefront sensor device, William et al. Have measured complex aberrations that cannot be calibrated by eyeglasses, contact lenses, other ocular devices, or surgical modifications of the eye. And I was able to calibrate.

Liang et al., "Abnormal vision and high resolution retinal images through adaptive optics"("American Journal of Optophysiology" (J.Opt.Soc.Am.A.) (1st
4, pp. 2884-2892, 1997) describes the use of adaptive optics to measure and calibrate the monochromatic aberrations of the eye. Calibrating the monochromatic aberrations provided with the six folds in the higher terms increases the contrast sensitivity when observing a 27.5 cycles / degree (cpd) monochromatic analysis grating through a 6.0 mm pupil. However, only contrast sensitivity has been measured in monochromatic light and at one spatial frequency, which is not representative of normal daily viewing conditions.

It is also known that the human eye suffers from monochromatic aberrations. There is much literature on attempts to analyze the effects of monochromatic aberrations of vision. Campbell and Gwish, Physiology Journal (J. Physiol.) No. 192, pages 345 to 358 (1967).
Have been reported with respect to monochromatic focus (longitudinal monochromatic aberration) differences with insignificant improvements in contrast sensitivity between white and monochromatic light.

[0006] "Optometry and Sight Science" by Thibos et al., No. 68,
No. 8, pp. 599-607 (1991), raises the question of how monochromatic aberrations have a significant effect on visual acuity and, if so, why and how much.

[0007]

[Non-Patent Document 1] US Journal of Optical Physiology (J.Opt.Soc.Am.A.) (Vol. 11, No. 7, No. 19)
(P. 47 to 1957, July 1994)

[Non-patent document 2] "Supernormal visual acuity and high resolution retinal image through adaptive optics" by Liang et al., US Optical Physiology Journal (J.Opt.Soc.Am.A.) (
(Vol. 14, pp. 2884 to 2892, 1997)

[Non-Patent Document 3] Campbell and Gwish's "Physiology Journal (J. Physi
ol. ) No. 192 ”, pages 345 to 358 (1967)

[Non-Patent Document 4] "Visual measurement and visual science" by Thibos et al., No. 68, No. 8, 599 to 607 (1991).

[Patent Document 1]           US Pat. No. 5,777,719

[0008]

[Problems to be Solved by the Invention]

The conclusions are listed below. a) Monochromatic aberrations in the axial (longitudinal) direction only cause a moderate decrease in contrast sensitivity and a secondary loss of visual acuity; b) Monochromatic difference in magnification has little effect on visual performance. And c) for oblique monochromatic aberrations, the visual acuity of the depression becomes important only when the pupil is laterally displaced. It mostly accounts for the unnoticeable impact of monochromatic aberrations in visual acuity, which is most rigorous at both ends of the eye where the optical spectral (afterimage) sensitivity of the eye is low.

Also, many studies investigating the effects of monochromatic aberrations of visual acuity and retinal image quality do not consider the synergistic effect of monochromatic aberrations on the performance of visual acuity and high-term monochromatic aberrations.

In an effort to improve visual acuity, the inventor has recognized the need to evaluate visual acuity performance under normal viewing conditions, and as a result, the second term aberration, the high term aberration , Or monochromatic aberration, or calibration of either one or a combination thereof is effective in improving visual acuity performance. Therefore, it is necessary to evaluate the influence of aberration on human visual acuity and provide a retinal image through visual acuity improvement and aberration calibration.

[0011]

[Object of the Invention]

FIELD OF THE INVENTION The present invention relates generally to embodiments of devices and methods for improving human visual performance and retinal imaging, and in particular, such devices and methods provide high visual acuity and high human eye performance. It evaluates and improves the image of the retina by a number and is based on a combination of high term monochromatic and chromatic aberrations.

[0012]

[Means for Solving the Problems]

To achieve the above object, the invention according to claim 1 calibrates (corrects) a monochromatic aberration for a human visual acuity with a high number of eyes, and calibrates a chromatic aberration for a human visual acuity with a high number of eyes. And a method of improving the visual acuity of a person including.

In a preferred embodiment of the invention according to claim 2, the process for calibrating the monochromatic aberration with a high number of terms in the eye is a radial zenicho mode with a number of terms higher than the third. Characterized by a method of improving eyesight of a person.

According to a third aspect of the present invention, which depends on the second aspect, the process of calibrating the monochromatic wave aberration with a high number of terms in the eye is performed in the radial zener mode of the fifth to the tenth highest number. Is characterized by a method of improving the visual acuity of a person.

A fourth aspect of the present invention, which depends on the first aspect, is characterized by a method for improving the visual acuity of a person, which further includes a process of correcting defocus and astigmatism for the visual acuity of the person.

In the invention according to claim 5 dependent on claim 1, the processing for calibrating the monochromatic aberration with a high number of terms in the eye is performed by an eye represented by a radial zenic mode with a higher number of terms. And a method of improving a person's visual acuity including the process of measuring the wave aberration of the.

According to a sixth aspect of the present invention, which is dependent on the first aspect, the process of calibrating the monochromatic aberration with a high number of terms in the eye is performed by a radial zenic mode with a fifth to tenth highest number of terms. A method of improving a person's visual acuity including the step of measuring the wave aberrations of the eye.

The invention according to claim 7 when dependent on claim 1, wherein the process of calibrating monochromatic aberrations with a high number of terms in the eye has a step analysis diagram adapted to calibrate said aberrations appropriately. A method for improving a person's visual acuity including the step of providing an ophthalmic device.

The invention according to claim 8 dependent on claim 7 is the apparatus for ophthalmology, which comprises at least one of a contact lens, an intraocular lens, an ophthalmic inlay, and an ophthalmic onlay. Features a method for improving a person's eyesight.

In the invention according to claim 9 dependent on claim 1, the step of the process of calibrating the monochromatic aberration with a high number of terms of the eye is performed to calibrate the monochromatic aberration with a high number of terms of the eye. And a method of improving a person's visual acuity, which includes a process of changing a characteristic of a human eyeball.

In the invention according to claim 10 dependent on claim 1, the step of the process of calibrating the chromatic aberration of the eye includes the bandwidth of the spectrum (afterimage) of the incidental condition of visible light on the human eyeball. And a bandwidth is in the range of approximately 10 nm to 150 nm beyond the visible spectrum to improve human vision.

In the invention according to claim 11 dependent on claim 10, the step of calibrating the chromatic aberration of the eye further provides a bandpass filter for calibrating the chromatic aberration of the eye. A method of improving a person's visual acuity, including treatment, is featured.

The invention according to claim 12 that depends on claim 10 provides a pass filter that passes a long wavelength in the step of calibrating the chromatic aberration of the eye, in order to calibrate the chromatic aberration of the eye. And a method of improving a person's visual acuity including a process of performing.

In the invention according to claim 13 which depends on claim 1, the process of calibrating the chromatic aberration of the eye includes the process of apodizing the human pupil (optical image transmission control) to improve the human visual acuity. The method is characterized by

According to a fourteenth aspect of the present invention, which depends on the thirteenth aspect, the process of apodizing the pupil (optical image transmission control) is performed uniformly between the edge (edge portion) and the center of the pupil. A method for improving a person's visual acuity, which provides a non-constant amplitude transmission of light.

The invention according to claim 15 dependent on claim 14 is characterized in that the transmission of light increases from the edge (edge portion) of the pupil to the center, thereby improving the visual acuity of a person. .

The invention according to claim 16 dependent on claim 14 is characterized in that the process of apodizing (optical image transmission control) the pupil is a method of improving the human visual acuity which is a function of wavelength. To do.

The invention according to claim 17 subordinate to claim 10 further includes a method for improving visual acuity of a person, which further comprises an apodization (optical image transmission control) filter for correcting the aberration. Is characterized by.

The invention according to claim 18 dependent on claim 17 is such that the apodization (optical image transmission control) filter supplies non-uniform (constant) amplitude transmission of light across the pupil. It features a method of improving the visual acuity of a person.

The invention according to claim 19 dependent on claim 18 is characterized in that the amplitude transmission improves the visual acuity of a person increasing from the edge (edge portion) of the pupil to the center.

The invention according to claim 20 subordinate to claim 1 is a method for improving visual acuity of a person, wherein correction of chromatic aberration of an eye is to collectively supply monochromatic aberrations of a high number of eyes. Is characterized by.

The invention according to claim 21 subordinate to claim 1 is a method for improving the visual acuity of a person, wherein the correction of the chromatic aberration of the eye supplies a high number of monochromatic aberrations of the eye to the outside. Characterize.

The invention according to claim 22 comprises an optical element selected from at least one of a contact lens, an intraocular lens, an inlay, and an onlay, and the element has a high eye number for the human eye. Has a surface shape adapted to calibrate the wave aberration of ## EQU3 ## and wherein the element is an ophthalmic device for improving the visual acuity of a person adapted to calibrate the chromatic aberration.

The invention according to claim 23, which is dependent on the above-mentioned claim 22, is characterized in that the correction of the wave aberration of the high-numbered monochromatic eye is the same as that of a person who is in a radial zenoic mode with a higher number than the third. Characterized by being an eye device for improving eyesight.

The invention of claim 24, which is dependent on claim 23, is characterized in that the correction of the wave aberration of the high-number monochromatic eye includes the radial zeninic mode of the fifth to tenth states. It is an ophthalmic device that improves the visual acuity of a person.

The invention as claimed in claim 25, which is dependent on claim 22, is characterized in that the element adapted for calibrating the chromatic aberration is an eye device for improving the visual acuity of a human being an optical filter. To do.

The invention according to claim 26, which depends on claim 25, is characterized in that the optical filter is an eye device for improving the visual acuity of a person, which is a neutral intensity (density) filter. .

A thirty-seventh aspect of the invention, which depends on the twenty-fifth aspect, is characterized in that the optical filter is a band-pass filter which is an eye device for improving human visual acuity.

A thirty-eighth aspect of the invention according to the twenty-fifth aspect is characterized in that the optical filter is a long-pass filter which is an eye device for improving the visual acuity of a person.

The invention according to claim 29, which is dependent on claim 25, is the eye device for improving the visual acuity of a person, wherein the optical filter is an apodization (optical image transmission control) filter. And

The invention according to claim 30, which depends on claim 29, is such that the apodization (optical image transmission control) filter is uniform (constant) between the edge (edge portion) and the center of the pupil. It is an ophthalmic device for improving the visual acuity of a person, which performs non-amplitude transmission of light.

A thirty-first aspect of the present invention according to the thirty-first aspect, which is dependent on the thirty-ninth aspect, is the ophthalmic device for improving the visual acuity of a person, wherein the amplitude transmission is reduced from the center of the pupil to the edge (edge portion). It is characterized by

According to a thirty-second aspect of the present invention that is dependent on the thirtieth aspect, the apodization (optical image transmission control) filter is spectrally dependent, and includes an edge (edge portion) and a center of the pupil. It is an ophthalmic device for improving the visual acuity of a person, which performs non-constant light amplitude transmission during the period.

The invention according to claim 33, which depends on claim 32, is such that the attenuation of light from the center of the pupil to the edge (edge portion) is increased by the wavelength away from the reference wavelength. It is an ocular device for improving.

In the invention according to claim 34, which depends on claim 29, the apodization (optical image transmission control) filter has an expression form of A (r) = exp (−r ⁴ / 2σ ² ). It is an eye device that improves the visual acuity of a person, which is represented by a (transcendental) Gaussian function higher than usual.

A thirty-fifth aspect of the invention according to the thirty-ninth aspect of the present invention is that the apodization (optical image transmission control) filter has an annular color absorption whose density increases from the center of the pupil to the edge (edge portion). It is an ophthalmic device that improves the visual acuity of a person including a material.

The invention according to claim 36, which is dependent on claim 35, is characterized in that the apodization (optical image transmission control) filter has a total band of approximately 500 nm to 650 nm. It is an ocular device for improving.

In the invention according to claim 37, which depends on claim 29, the apodization (optical image transmission control) filter includes a plurality of adjacent annular shaped filters, and each annular filter is provided. Is an ophthalmic device that improves a person's visual acuity, which is defined by a bandpass having a narrower bandwidth than adjacent small rings.

The invention according to claim 38, which depends on claim 29, is characterized in that the apodization (optical image transmission control) filter is such that a light does not penetrate and a ring having an inner diameter and an inner diameter. And a portion having a pass width having a bandwidth of approximately 550 nm to 610 nm between the outer diameter and the outer diameter, the ophthalmic device improving the visual acuity of a person.

In the invention according to claim 39, which depends on claim 38, the inner radius is 2
An ophthalmic device that improves the visual acuity of a person equal to or less than mm.

The invention according to claim 40, which is dependent on claim 29, is characterized in that the apodization (optical image transmission control) filter comprises a plurality of adjacent annularly shaped filters, the filter comprising: Providing a first annular ring with a non-penetrating central radial portion and a long pass filter, a second annular ring larger than and adjacent to the first annular ring providing a band pass filter improves the visual acuity of the person It is a device for the eye.

The invention according to claim 41, which is dependent on claim 40, is characterized in that the long-pass filter performs transmission of a wavelength exceeding approximately 510 nm, and the band-pass filter performs transmission of approximately 550 nm to 610 nm. It is an ophthalmic device that improves the visual acuity of a person.

The invention according to claim 42, which is dependent on claim 29, is characterized in that the apodization (optical image transmission control) filter is an ophthalmic device for improving the visual acuity of a person, which comprises a long-pass filter. And

The invention according to claim 43, which is dependent on claim 42, is the eye device, wherein the long-pass filter substantially improves the visual acuity of a person who transmits a wavelength of a reference wavelength of approximately 555 nm or more. Is characterized by.

The invention described in Item 44 is an optical system system for improving the visual acuity of a person, which comprises a phase compensation element (means) having a high number of terms and an amplitude correction element (means) for light. Characterize.

According to a forty-fifth aspect of the present invention, which depends on the forty-fourth aspect, the phase compensating means and the light amplitude correcting means having a high number of terms are optical components that improve the visual acuity of a human being an existing general optical component. It is characterized by being a system.

The invention according to claim 46, which depends on claim 44, improves the visual acuity of a person, which is an optical component provided separately for the phase compensating means and the light amplitude changing means having a high number of terms. It is an optical system.

The invention according to claim 47, which is dependent on claim 44, is an optical system for improving the visual acuity of a person whose high-number phase compensator is a distorted (deformed) mirror. It is characterized by An invention according to claim 48, which depends on claim 44, is an optical system in which the phase compensating means having a high number of terms improves the visual acuity of a person who is a liquid crystal device.

The invention as set forth in claim 49, which depends on claim 44, is characterized in that the phase compensating means having a high number of terms is an optical system for improving the visual acuity of a person who is a contact lens.

The invention according to claim 50, which is dependent on claim 44, is characterized in that the phase compensating means having a high number of terms is an optical system system for improving the visual acuity of a human being an intraocular lens.

The invention according to claim 51, which is dependent on claim 44, is that the phase compensating means having a high number of terms is an optical system for improving the visual acuity of a person who is a reformed (reformed) cornea. Characterize.

The invention according to claim 52, which is dependent on claim 44, is characterized in that the phase compensating means having a high number of terms is an optical system that improves the visual acuity of a person who is an ophthalmologic inlay.

The invention as set forth in claim 53, which depends on claim 44, is characterized in that the phase compensating means having a high number of terms is an optical system system for improving the visual acuity of a person who is an ophthalmologic onlay.

The invention according to claim 54, which is dependent on claim 44, is characterized in that the light amplitude changing means is:
It is characterized in that it is an optical system that improves the visual acuity of a person who is a filter.

The invention according to claim 55, which is dependent on claim 54, is characterized in that the filter is an optical system for improving the visual acuity of a person, which is a filter having at least one pass band and a long-pass filter. To do.

The invention according to claim 56, which depends on claim 44, is characterized in that the light amplitude changing means is:
It is an optical system system that improves the visual acuity of a human, which is the pupil of a person who has undergone apodization (optical image transmission control).

The invention according to claim 57, which depends on claim 56, is characterized in that the apodized (optical image transmission control) pupil has a non-constant light between the edge (edge portion) and the center of the pupil. It is an optical system system that improves the visual acuity of a person who supplies the amplitude transmission of.

In the invention according to claim 58, which depends on claim 56, the apodized (optical image transmission control) pupil is spectrally dependent, and the edge (edge portion) and the center of the pupil are centered. It is an optical system system for improving the visual acuity of a person, which performs non-constant amplitude transmission of light between and.

The invention of claim 59, which is dependent on claim 45, is characterized in that the general optical component comprises at least one contact lens, intraocular lens, inlay, and onlay. It is an optical system system for improving.

The invention according to claim 60, which depends on claim 46 above, is characterized in that the phase compensating means comprises:
At least one contact lens, an intraocular lens, an inlay, and an onlay, and a reformed (recreated) cornea present, wherein the optical amplitude modifying means is at least one contact lens, intraocular lens, inlay, and An optical system for improving the visual acuity of a person, which is an external optical component used together with an on-ray and a phase compensation means.

According to a sixty-first aspect of the invention dependent on the forty-fourth aspect, the phase compensating means and the light amplitude correcting means are arranged on the optical axis of the optical system. It is an optical system system for improving.

The invention according to claim 62, which is dependent on claim 1, further comprises the process of measuring monochromatic aberration and chromatic aberration of the eye with a high number of at least one eye. It is a method of improving.

According to a sixty-third aspect of the present invention, the generating means for generating a reflection point source image of the retina of a living eye, the receiving means for receiving the reflection point source image, and the point source image correspond to each other. Converting means for converting to a digital signal; calculating means for calculating a high number of monochromatic aberrations using the digital signal; and the living eye to generate a disc (surface) image of the retina. An illumination means for illuminating the disc (surface) of the retina, and the high-number phase-compensating optics in the optical path of the system are adjusted to calibrate the high-number monochromatic aberrations. , An optical amplitude modifying element is placed in the optical path of the system to calibrate the chromatic aberration and provides an image of the disc (surface) of the reflected retina after calibration of high number of monochromatic and chromatic aberrations Offering hands for When, characterized in that an optical system system for living generate high resolution images of the retina of the eye are provided with.

The invention according to claim 64, which is dependent on claim 63, provides the human visual acuity in which the phase compensation optical element with a high number of terms is one of a distorted mirror, a liquid crystal device, and a MEMS device. It is an optical system system for improving.

The invention according to claim 65, which is dependent on claim 62, is characterized in that the optical amplitude modifying element is one of an artificial apodization (optical image transmission control) element and an optical filter. It is characterized by being an optical system that improves visual acuity.

According to a sixty-sixth aspect of the present invention, the steps of generating a reflection point source image of the retina of a living eye, converting the point source image into a corresponding digital signal, and using the digital signal Calculating a high number of monochromatic aberrations; illuminating the surface of the retina of the living eye to create a disc (surface) image of the retina; Blocking the (surface) image, the phase compensating optics being adjusted so that wavefront compensation for said wave aberrations is provided for the living eye; Providing a light amplitude correction means, and a method of generating a high resolution image of the retina of a living eye including:

The invention according to claim 67, which depends on claim 66 above, irradiates the surface of the retina with
A method of producing a high resolution image of a living retina using a broadband light source.

The invention as claimed in claim 68, which is dependent on claim 66, is characterized in that the step of correcting chromatic aberration is an artificial apodization (optical image transmission control) pupil of the optical system. It is a method for generating a high-resolution image of the retina of a living eye.

[0079]

DETAILED DESCRIPTION OF THE INVENTION

An embodiment of the present invention is an optical system for improving human visual acuity that includes a high number of phase compensation elements and a light amplitude correction element. While the light amplitude modifying element is used to provide the calibration for monochromatic aberrations, the high-term phase compensation element is used to provide the calibration for the high-term monochromatic aberrations. In this embodiment of the invention, the high term phase compensating element and the optical amplitude modifying element provide for a common optical element. Alternatively, the high term phase compensating element and the optical amplitude modifying element may be provided in separate optical elements.

Another embodiment of the present invention is an ophthalmologic element for improving human vision. This element has at least one shape adapted to calibrate the measured high-term monochromatic ophthalmic aberrations. Moreover, the ophthalmic element has a non-uniform transmission over at least a portion of the surface for calibrating ophthalmic monochromatic aberrations. In this embodiment,
The pupil diameter of the eye is effectively reduced with artificial apodization (optical image transmission control) to counteract the deleterious effects of aberrations on the visual acuity performance of the eye.

In another embodiment, an improved high resolution retinal image is provided. While the image quality is enhanced by calibrating high-numbered aberrations and monochromatic aberrations, the system for producing this image is also expected to have the effect of using a broad band light source to increase the emission. it can.

The method of the embodiments of the present invention improves the measurable visual acuity benefit of humans and calibrates high ophthalmic high term monochromatic aberrations, as well as chromatic aberrations, preferably and substantially. Including axial chromatic aberration. Preferred methods for calibrating high-number monochromatic aberrations are distortion mirrors or other phase compensation elements, such as LCD (Liquid Crystal Device; hereinafter) or MEMS (Microelectronic Micromechanical Systems; Is a contact lens by refractive surgery or photoablation, an intraocular lens (Intra-Ocular lens; Intra)
-Ocular Lenses; hereinafter abbreviated as "IOL"), including inlays (to be placed inside the eye), onlays (to be placed on the eye), or corneal formation, for example, produced by a typical eye. Applied to provide appropriate phase compensation to calibrate the wavefront of aberrations.

In order to provide a precise and precise description of the means for solving the problem, the following is set forth to define the meaning of the terms used throughout the detailed description and claims. Apodization (optical image transmission control) relates to non-uniform amplitude transmission of light across the radius of the pupil, ie, between the center of the pupil and the edge of the pupil. Higher number of monochromatic aberrations can be seen by the third and higher number of Zeemicle polynomials (
Pistons, tips, and tilts), ie, optical aberrations expressed in aberrations equivalent to those described in other meter methods known to those skilled in the art. And, the focus is particularly on the optical aberrations represented by the radial Zemickle modes (excluding piston, tip, and tilt) of the fifth or tenth terms or their equivalents.

Chromatic aberration is conventionally defined, but is preferably and substantially axial or longitudinal chromatic aberration, as will be appreciated by those skilled in the art.

The visual performance described here is a quality (qualitative) measure of how well a human can see. Visual benefit (VB) is used to demonstrate a quantitative measure of visual performance. The benefits of vision are expressed in terms of contrast sensitivity and visual acuity, as will be appreciated by those skilled in the art. More specifically, visual benefit is equivalently defined in terms of psychophysical visual benefit (VB _psy ) and optical visual benefit (VB _opt ).

[0086]

[Equation 1]

Here, in Expression 1, CSF is defined as a function of contrast sensitivity,
w / HOC means having a high term number aberration calibration, w / oHOC means not having a high term number calibration, and MTF (spatial frequency characteristic; It relates to the transfer function of modulation. With respect to the results described below for the case of calibrating only a high number of monochromatic aberrations (Zemicle modes from the third term to the tenth term), the advantage of optical vision is defined as:

[0088]

[Equation 2]

Then, for the case of calibrating both high-numbered monochromatic aberrations and axial chromatic aberrations, the advantages of optical vision are defined as follows.

[0090]

[Equation 3]

In both cases, defocus and astigmatism (second term Zeemickle mode) were calibrated as necessary to provide baseline visual performance. An optical system relates to one or more optical elements related to human vision, including but not limited to:
A cornea, contact lens, IOL, ophthalmic inlay, ophthalmic onlay, or external element, such as a distortion mirror or spectacle lens alone or in combination with other optical elements, depending on the desired application and practical considerations. Including.

The high-number phase compensating element is not limited to, but is not limited to, to bend the substantially planar wavefront, in other words, to provide a calibration for high-number aberrations. Any of the optical elements described above having a surface whose shape is modified in response to chromatic aberration wavefront data. The light amplitude modifying element relates to a structure that redistributes light by, but not limited to, diffraction, interference, aspiration, transmission, or filtration to provide compensation or calibration of ophthalmic chromatic aberrations.

In summary, the present invention provides high-term monochromatic and chromatic aberrations of the eye that outweigh the visual benefits obtained by calibrating either high-number monochromatic or chromatic aberrations alone. An apparatus and method for obtaining visual benefits by calibrating. It has been observed by the inventor that the beneficial effects provided by calibrating a high number of monochromatic aberrations are diluted in the presence of chromatic aberrations under normal viewing conditions. In other words, the benefits of calibrating both high term monochromatic ophthalmic aberrations and ophthalmic chromatic aberrations are far greater than the benefits obtained by calibrating only one of the aberrations. Moreover, the above-mentioned dilution or improvement is more effective for large pupil sizes of 3-8 mm than for small pupil sizes of less than 3 nm. Based on such findings, known to those skilled in the art,
Calibrates a high number of monochromatic aberrations of the eye with DM (Doteranamoles; indistinguishable color, hereinafter DM), contact lenses, IOLs, cornea formation, ophthalmic inlays, ophthalmic onlays, and other ophthalmic devices or techniques. However, additional calibration in the eye can further improve the visual benefits.

The present invention relates to a device and a method for improving the retinal image in which the above-mentioned idea is used. These and other objects and certain effects of the present invention will be described in the following detailed description,
It will be more complete with the associated drawings and claims.

High term monochromatic ophthalmic aberrations appear in the distorted (non-planar) wavefront of the light emitted from the eye. As those skilled in the art will appreciate, these wavefronts can be returned to a substantially planar wavefront by phase compensation on the wavefront. The high number of phase compensation elements are preferably useful to provide the required phase compensation. In a preferred example, an ophthalmic instrument or device having an appropriate phase profile (eg, surface profile) over at least a portion of the surface of the instrument or device is provided to calibrate high term monochromatic aberrations. ing. For example, such appliances include distortion mirrors, LCDs, MEMS.
Includes devices, contact lenses, IOLs, ophthalmic inlays, ophthalmic onlays, and reformed corneas.

On the other hand, monochromatic aberrations are affected by the light amplitude distribution across the pupil area, with or without spectral dependence. In the preferred example, a spectral filter or diffractive light surface is provided to calibrate for monochromatic aberrations. More preferably, artificial apodization of the pupil (optical image transmission control) is provided, which will be described in detail below. Artificial apodization (optical image transmission control) is also
There are effects that can be used to improve the retinal image.

One embodiment of the present invention relates to an optical system for measuring and improving human visual acuity, including high term number compensating elements and optical amplitudes calibrating the elements. In the example of this embodiment, referring to FIG. 1, an optical system 10 applied to measure and calibrate wavefront aberrations.
The distortion mirror (DM) 118 used in FIG.
The DM (discussed in detail below) has a phase shape that allows the shape to be distorted and compensates for the aberration phase shape of the wavefront reflected from the eye. Alternatively, an LCD or MEMS device (not shown) instead of DM can provide the appropriate phase compensation recommended by one of ordinary skill in the art.

Referring to FIG. 3, a preferred optical system 190 for correcting human vision is a contact lens 200 with a customized or custom surface shape to provide an appropriately high term phase compensation. (Or an IOL (not shown), an ophthalmic inlay (not shown), an ophthalmic onlay (not shown), or a reshaped retina (not shown)) to provide a high number of phase compensation elements. Including. The compensated phase shape arises from the wavefront in the form of Zemicle coefficient data. This data is shown in Figure 1.
Produced by the active optics 10 outlined in (detailed below).
. The final wavefront calibration signal from the computer 132 to the DM 118 is also the lens manufacturing system, i.e. where the calibrated wavefront aberration data can be used to produce the appropriate surface on the selected high term phase compensation element. It can be transmitted to the laser surgical platform 152. Techniques for producing or calibrating contact lenses, IOLs, inlays, or onlay surfaces are known to those of skill in the art, such as lathes,
Includes casting, molds, and laser machines. Refractive surgery or laser ablation is the preferred technique for properly forming the human cornea.

A typical light amplitude calibrating element according to an embodiment of the invention is represented by the interference filter 136 in FIG. In a more practical and preferred example, the light amplitude modification involves artificially apodizing the human pupil through an apodization (optical image transmission control) filter, as described below. Done by The apodization (optical image transmission control) described here refers to the non-uniform amplitude transmission of light as a function of pupil radius. Natural apodization in visual acuity (optical image transmission control) is known for the Stiles-Crawford effect. Due to the waveguide nature of the photoreceptors of the eye, light entering the periphery of the pupil is less efficient at stimulating the retina than light passing through the center of the pupil. However,
In theory, apodization (optical image transmission control) effectively reduces pupil diameter, but Stiles-Crawford apodization (optical image transmission control) impacts aberrations on image quality. Is almost never reduced. In particular, apodization (optical image transmission control) is a point spread function (point spread function; point) that increases the modulation from a low position to a central spatial frequency.
The height of the side lobes in the spread function is reduced. This generally increases the error tolerance, so the invention is particularly applicable to defocus and resulting axial chromatic aberrations.

The optical properties of a system (eg, contact lens plus eye) can be summarized by means of a general pupil function that defines the next exit pupil.

Ρ (r, θ) = A (r, θ) exp [(i2π / λ) W (r, θ)] ... (
1)

Where A (r, θ) is the amplitude transmitted through the pupil point (r, θ) and W (r, θ) is the wave aberration. With conventional contact lenses, W (r, θ)
Means high number of aberrations plus chromatic defocus for each wavelength. In a contact lens customized for a high number of aberrations, W (r, θ) is
Indicates the inherent monochromatic aberration plus chromatic aberration. In both cases, a suitable filter A (r) is used in contact lenses to gradually reduce the optical transmission from the center of the lens to the edge, so that the magnitude of the aberration increases the pupil radius and thus the aberration of the retinal image. It reduces the impact of. To calibrate the chromatic aberration, the filter
A (r; λ), with a different dilution for each wavelength, should be wavelength dependent.

Different apodization (optical image transmission control) functions are available in Gossian (Gauss)
It is known to those skilled in the art that (Gaussian) apodization (optical image transmission control) is one of the most common. However, aberrations increase more immediately at the edge of the pupil with respect to the center, so another feature characterized by a smooth slope around the center of the steepness near the edge of the pupil is Gaussian. Apodization (
Optical image transmission control) function, but with a significantly increased level of brilliance. Therefore, in the preferred embodiment of the present invention of the Gaussian filter, the super-Gaussian function is represented by the following equation.

A (r) = exp (−r ⁴ / 2σ ² ) ... (2)

Here, r is a pupil radius, and σ is an apodization (optical image transmission control) parameter related to the width of the apodization (optical image transmission control) function. Figure 4
Figure 6 shows the amplitude transmitted with the super-Gaussian transmission function of equation (2) for various pupil radii for different values of the parameter σ. In contrast, FIG. 5 shows the transmitted amplitude of a typical value of σ for the Styles-Crawford effect formed by the Gaussian function of:

[0106] A (r) = exp (-ρln10.r 2/2)

The apodization (optical image transmission control) filter exemplified in the present invention will be described below. <Typical Filter First> Referring to FIG. 6, the values of some parameters of the visible wavelength spectrum are shown for the first typical apodization (optical image transmission control) filter of the present invention. Has been done. In this case, apodization (optical image transmission control) is not performed within the 20 nm interval centered at the reference wavelength of 575 nm. FIG. 7 shows the values of the light intensity transmitted to this filter through different pupil radii for each wavelength. FIG. 8 shows the overall transmission through all pupil holes for all wavelengths. Although a particular spectral bandwidth is shown, it is preferred that the transmission region of a particular spectrum be selected based on the desired application. For example, if increased night vision is desired, the transmission region of the spectrum is moved to better match the visual sensitivity of the red color of the eye.

An exemplary optical device 190 in the shape of a custom contact lens that is artificially apodized (optical image transmission control) according to an embodiment of the present invention is shown in FIG.
And schematically in FIG. The contact lens 200 has an optical zone defined by r ₃ and provides the high term number of monochromatic aberrations described above. The apodization (optical image transmission control) filter 202 according to the exemplary filter first shown in FIG. 9 includes a center 20 of the lens 200 along an optical axis (not shown) of the lens.
It is in line with 4. Wavelength dependent apodization introduces a color absorber, eg, dye, across the optical band of the contact lens 200 so that the intensity increases from the center 204 of the optical portion of the lens to the edge 208. Can be achieved. Those skilled in the art will appreciate that there are various ways to create such filter shapes. For example, contact lens material initially provided in the shape of a cylindrical rod is impregnated with a suitable dye that diffuses the lens material. The desired strength profile is achieved by repeating appropriate diffusion and controlling other known parameters.

<Typical Filter Second> In the example of the apodization (optical image transmission control) filter shown in FIG.
A suitable filter material is a concentric annular ring 220, 221, above the lens surface.
It is applied to 222 etc. In this way, the filter material provides a bandpass filter in each ring, but each ring has a narrower bandwidth as the distance to the center of the lens increases. For example, from the lens center (r = 0) to r =
Up to 0, there is no filter, but filters from 0.5 to 1 mm have the spectral shape shown in FIG. 7 for a particular radial position, as well as various external radii to the edge of the lens. Different annular radii and filter shapes depending on the application are well within the scope of the invention.

Typical Filter Third> With reference to FIG. 11, the second simplest case of the exemplary filter described above is the use of a single ring. As shown, the filter is the r of the optical portion of the lens.
= 2 mm and up to the edge 208, avoiding short wavelengths entering through a pupil larger than 4 mm diameter. Preferably, the filter has a bandwidth λ = [550
-610 nm]. As mentioned above, other radii and bandwidths are applicable.

Exemplary Filter Fourth> In an example of this embodiment of the invention, the contact lens 200 illustrated in FIG. 3 combines two filters to provide two different zones of the contact lens, eg, the lens. There is no filter in the central 2 mm diameter, resulting in a long pass filter (λ> 510 nm) in the zone between 2 mm and 4 mm diameter and a pass filter for diameters larger than 4 mm (λ = 510-610 nm).

<Typical Filter Fifth> Alternatively, apodization (optical image transmission control) takes the form of a long-pass filter with respect to the band-pass filter described above. This is because only wavelengths equal to or shorter than the reference wavelength are removed. FIG. 13 may be for a typical filter first.

FIGS. 14 and 15 show respective exemplary filters 1 and 5 and exemplary filters 3 and 4 for calibrating a high number of monochromatic aberrations and for calibrating chromatic aberrations, respectively. White light M corresponding to the coupling optical element (eg, contact lens)
TF is shown. All data are submitted for a 6 mm artificial pupil diameter.

FIG. 16 shows the MTF of white light for different apodization (optical image transmission control) filters of the present invention when either monochromatic or chromatic aberrations are not calibrated. In this case, the visual benefit is similar to that obtained with a single 4 mm diameter centered stop on the contact lens. As shown, this result is inferior to that shown in FIGS.

FIG. 17 shows the advantages of customized coma and spherical aberrations according to the invention, and the additional advantages when the lens combines filters for chromatic aberration calibration.
This graph shows that only some of the high-numbered monochromatic aberrations provide visual benefits when calibrated with chromatic aberration calibration.

In a preferred embodiment, the optical system for improving human vision comprises a high number of phase compensating elements and optical amplitude modifying elements common to the optical components or materials.
Such a system is shown in the optics of FIGS. This integrated system is preferred when the high-term phase compensating element is either a contact lens, IOL, inlay, or onlay and is not a reformed cornea. It is effective that the optical amplitude correction element is one of the apodization (optical image transmission control) filters described above.

Alternatively, the optical system for improving human visual acuity may include a high number of phase compensation elements and optical amplitude correction elements separately in the optical component or material. In this system, one or more high-number phase compensating elements are used, for example, in connection with the high-number phase compensating elements to be used in an apodization (optical image transmission control) or filtered spectacle. The above can be included in combination with the lens. Preferably, separate flat optics will be used when the high number phase compensating element is a re-formed cornea.

Other embodiments of the present invention provide greater than normal retinal image quality for high resolution retinal images. FIG. 2 schematically illustrates a retinal imaging system 30 that may be used to provide a subject with superior or better retinal image quality and may be used to provide a high resolution image of the retina 109 of the eye 107. The optical system 30 is substantially similar to the optical system 10 of FIG. 1 except for the broadband light source 300 for emitting the retina 109 and the optical path 155 leading to the second CCD camera 156 for capturing the retinal image. In this embodiment, broadband retinal emission is provided by the Kipton flashlamp 300. The Kipton flash lamp 300 is
It is typically imaged with a 4 millisecond flash, which causes the retinal disc on the retina 109, preferably 1 degree or more in diameter, to fire. The image of retina 109 is reflected by a distortion mirror 118 already formed to compensate for the high-term monochromatic aberrations of the eye described with respect to FIG.

Immediately following the apodization (optical image transmission control) filter 137, the retinal image C
By a mirror 125 through an artificial pupil 134 focused on the CD 156,
Light is reflected. The improved retinal image (and corresponding subject retinal image capability is improved in US Pat. No. 5,777,719 to William et al. By calibration of chromatic aberration provided by an apodization (optical image transmission control) filter 137. The apodization (optical image transmission control) filter 137 is preferably described by any of the exemplified apodization (optical image transmission control) filters described above. One of ordinary skill in the art will provide such a filter, for example, by printing a preferred filter shape on a suitable material for coupling to optical system 30. The apodization (optical image transmission control) filter described above. Is the preferred device for calibrating the chromatic aberration in the retinal imaging system of FIG. Other filters, such as filters and interference filters, could be used, however, narrowing the bandwidth to a portion of the full visual bandwidth to reduce chromatic aberration will reduce the overall emission. It was observed that there was a drawback that reduced it, Figure 25 shows this effect from the field of view of visual acuity, however, 2x vision obtained over the full visual bandwidth (290 nm). A narrower bandwidth up to 50 nm (530 nm to 580 nm), which provided the advantage of, would reduce emission by about 50% with a loss of color vision.

With regard to the optical components, devices and systems described above, embodiments describe methods for improving human vision. The method involves calibrating a high number of ophthalmic monochromatic aberrations and calibrating ophthalmic chromatic aberrations, preferably substantial axial chromatic aberrations.

The high-term monochromatic aberration data is the optical system 1 to be adapted outlined in FIG.
Obtained from many subjects using 0. This device shares many features with the optics to be adapted illustrated and described in William US Pat. No. 5,777,719. The entire document is incorporated by reference and is set forth in FIG. In order to obtain aberration data, the subject's pupil must be either a mydricity (pupil diluent) (trade name) (1%) or cycloglu (
Diluted with Pupil Diluent (trade name) (1%). The position of the subject's head is then stabilized with the system 10 with a bite bar (not shown) for locating the position of the subject's eyes 107. An oversized light emitting diode 106 emitting at 790 nm is focused and reflected by a beam splitter 110 onto a retina 109 of the eye 107 as a point source. Light reflected from the retina passes through beam splitter 110 and is directed through lenses 112 and 116 onto distortion mirror 118, which is located at the interface with the pupil of the eye.

The distortion mirror 118 (Genetics; Xineticx; trade name or company name) is 3
7 lead magnesium niobate (lead magnesium niobate)
e; PMN) actuator is included to form a mirror surface and calibrate a high number of monochromatic aberrations. The light reflected from the distorting mirror 118 is focused by the lens 120 at a position corresponding to the hole 122 defined at the position where it joins the retina 109. At that time, the light is aimed at the lens 124 and the heart shack wavefront sensor 130
Of the lenslet array 126 of FIG.
The Hartshack wavefront sensor 130 includes a square array of 221 lenslets (focal length = 24 mm; internal lens space = 0.4 mm; adaptable optics available) with a tenth radius term number. Wave aberration data were provided up to (order) (Zenic coefficient of 63 excludes piston, tip, and tilt). The lenslet array 126 located at the cemented surface of the pupil of the eye forms an insubstantial image of the retinal point source on the CCD camera 128 located at the cemented surface with respect to the retina 109. Wavefront data from wavefront sensor 130 is processed by computer 132 and directed to distortion mirror 118 via feedback control loop 134. As shown in FIG. 1, the Mitsubishi Diamond Pro 710 CRT 138 is aligned at the interface with the retina 109 and is a diffraction grating or directional alphabet for the measurement and evaluation of contrast sensitivity and visual acuity. Was used to display visual stimuli to the eye in the form of letters.

The CRT screen appeared white with broadband, bimodal radiation nest spectra. The display has a 6 mm pupil 13 that provides a 1 degree viewing angle.
Observed through 4. Retinal emission was set at 57 Td. A neutral intensity filter was used as needed to even out the emission levels. Narrow bandwidth interference filter 1 with 10 nm bandwidth (FWHM) for center wavelength of 550 nm
36 was used for the measurement to calibrate the chromatic aberration. In other measurements, the longitudinal chromatic aberration was calculated as described in "Bedford Wyszekki, J. Opt. Soc. Am.
564-565) "(1957). It has been shown in the prior art that the longitudinal chromatic aberration is approximately 2 diopters (D) on the visual spectrum. The size of the colored defocus is shorter than that of the colored defocus (0.5D) at a long wavelength (700 nm) (400 n).
Large in m) (1.5D). However, the perceived chromatic aberration is shown in FIG.
As shown in 8, there is almost contrast for the reference wavelength of 555 nm. Chromatic aberration was also measured as would be appreciated by one of ordinary skill in the art.

In order to measure the contrast sensitivity, a fixed subject and defocus on a 16 cycle / degree grating was used with a Badal optometer while being calibrated with a prototype lens when astigmatism was required. Be calibrated in. Six different spatial frequencies of 2, 4, 8, 16, 24, and 32 cycles / degree are arranged in random order for the subject. The contrast threshold was determined using known adjustment methods.

To measure visual acuity, each of the four capitalized Es in four different directions were randomly displayed on the CRT 138 at 100 percent contrast. In case of defocus and astigmatism, it was calibrated as needed. The subject that responds to the letter and the direction of sharpness is measured at the lineweight of the letter for which 50% of the response is calibrated. Two different retinal emission levels of 57 Td and 575 Td are measured in monochromatic and white light, with a 6 mm pupil in four measurements.

<Advantages of Psychophysical Vision> FIGS. 19 (a) and 19 (b) respectively show (a) out-of-focus and astigmatism calibration, and (b) out-of-focus and astigmatism as well as high number of terms. Figure 6 shows the contrast sensitivity functions for two subjects (YY, GYY) after calibration of monochromatic aberrations, and (c) after calibration of both monochromatic and chromatic aberrations. The result is
Similar to both subjects. As shown, the contrast sensitivity obtained by calibrating a high number of monochromatic aberrations can be measured to be higher than when only out-of-focus and astigmatism are calibrated. In comparison, this illustrates that high-term monochromatic aberrations in the normal eye reduce visual performance. Also, as shown, calibrating both chromaticity and high term monochromatic aberrations results in a large flat increase in contrast sensitivity. The contrast sensitivities illustrated in FIGS. 19 (a) and 19 (b) show that chromatic aberration has the strongest dilution effect for the benefit of calibrating a high number of monochromatic aberrations.

FIGS. 20 (a) and 20 (b) show the psychophysical visual acuity from calibrating the high term number of monochromatic aberrations for the two subjects with respect to FIGS. 19 (a) and 19 (b). Show the benefits. The visual advantage for calibrating only a high number of monochromatic aberrations (open circles) is improved by two factors: average at 16 cycles / degree and 24 cycles / degree. The greatest visual benefit for the two subjects, respectively, is about 5 for YY and 3.2 for GYY at 16 cycles / degree when monochromatic and chromatic aberrations are calibrated (black circles).
Is a factor. The measurements described above were performed with a 6 mm diameter pupil size at 57 Td retinal emission.

In contrast, FIGS. 21 and 22 show measured data for contrast sensitivity and VB _psy , respectively, for subject GYY, along with a 3 mm pupil radius. It is observed that a modest advantage of calibrating high term aberrations and chromatic aberrations occurs at high spatial frequencies, corresponding to two factors of 16 cycles / degree in white light. The visual advantage of either calibrating only high-numbered monochromatic aberrations or both chromatic and monochromatic aberrations is less for a 6 mm pupil diameter.

23 and 24 show the respective visual acuity of high (575 Td) and low (57 Td) retinal emission levels for the seven subjects. Before taking this measurement, defocus and astigmatism are subjectively calibrated with the trial lens as needed. As shown in the figure, the monochromatic aberration-only calibration provides an average increase for 7 subjects by a factor of 1.2 at 575 Td and 1.4 at 57 Td. Calibration combining both aberrations improved the visual acuity by a factor of 1.6, as shown in FIG. Therefore, this is not only the contrast sensitivity but also the visual sharpness,
It further supports the observation that it is advantageous to calibrate a high number of monochromatic aberrations and that the increased advantage is realized by also calibrating the chromatic aberration.

[0130] <Advantages of optical visual> FIG 26 (a) and FIG. 26 (b) respectively, the average MTF and precalculated VB _opt is at 3mm pupil, wave aberration measurement of 17 subjects It was based on. Similarly, Figures 26 (c) and 26 (b) show similar information for a 6 mm pupil. Assuming that the calculation is a perfect correction,
There is no influence of monochromatic aberration or chromatic aberration after calibration. The transfer function of light modulation in monochromatic light was calculated from the wave aberration data of the subject measured with the active optics of FIG. The MTF of white light was obtained by summing each monochromatic MTF defocused by longitudinal chromatic aberration, offset by oblique chromatic aberration, and weighted by the optical spectral sensitivity of the eye at each wavelength. The value of the oblique monochromatic aberration of the depression was used according to the "Visual Acuity Study" by Thibos et al., No. 30, 33-49 (1990). Monochromatic MTF is calculated from 405 nm to 60 nm every 10 nm, assuming an evenly distributed energy spectrum.
Calculated to 9 nm. The reference wavelength without monochromatic aberration is 5
It was 55 nm. Before calibrating aberrations, the best focus of the eye on the grating is
Different for different spatial frequencies in both monochromatic and white light. We chose the amount of defocus to maximize the transfer function of the modulation of the 16 cycle / degree grating.

As shown in the figure, there is little optical visual benefit just to calibrate the chromatic aberration of the 3 mm pupil. The trifold increase in contrast sensitivity is
Only high number of monochromatic aberrations are observed when calibrated at 32 cycles / degree. On the other hand, referring to FIGS. 26 (c) and 26 (d), the calibration of high number of monochromatic aberrations only shows a larger optical visual of 5 × at high spatial frequency in the center for a 6 mm pupil. Has provided the advantage of. However, the optical visual benefits calculated from calibrating chromatic and monochromatic aberrations are substantially greater than those from calibrating only high-numbered monochromatic aberrations. The theoretical visual advantage is that the adapted optics is not able to do a full calibration, so
, And larger than the experimental data presented in FIG. Theoretical calculations indicate that calibrating a high number of monochromatic and chromatic aberrations over a large pupil diameter could increase optical quality on the retina by factors approaching 20 at 32 cycles / degree. To do. When either monochromatic aberrations or longitudinal aberrations are calibrated, uncalibrated aberrations dilute the advantages of other calibrations.

The methods of embodiments of the present invention provide high term monochromatic and chromatic aberration calibration in common optical components. For example, either the lens, IOL, inlay or onlay provides phase compensation and is artificially apodized to calibrate chromatic aberration.

Alternatively, the high term monochromatic and chromatic aberration calibrations are provided in separate optics. For example, any of the lenses, IOLs, inlays, onlays or reshaped corneas provide phase compensation, and apodized (filtered image transmission) or filtered spectacle lenses provide color calibration. It will be possible.

The present invention thus suggests, among other things, that the visual benefit is improved by calibrating the high-term monochromatic aberrations of the eye. When chromatic aberration is calibrated in addition to a high number of monochromatic aberrations, a flatter greater visual benefit is obtained. Actual devices and methods have been described for improving human vision. The measured improvements in visual acuity described above match well the visual benefits for full calibration and contrast sensitivity.

FIG. 27 shows that the sharpness of vision is theoretically increased by calibrating a high number of monochromatic and chromatic aberrations for a 6 mm pupil. Intersection of MTF and Neutral Threshold Curve (Green J. Physiol)
(1967)) predicts visual acuity. The multiplication numbers in FIG. 27 correspond to the advantages in visual acuity achieved by calibrating different aberrations.

In summary, the present invention is directed to a method and apparatus for improving human vision by combining and calibrating a high number of monochromatic ophthalmic and chromatic aberrations. Furthermore, the invention also relates to a system for improved retinal imaging.

While the preferred embodiments of the invention have been set forth above, those skilled in the art will appreciate that various variations of the invention, the details of which are set forth above, and the claims. It goes without saying that it can be considered without departing from the spirit and scope of the present invention.

[0138]

【The invention's effect】

Since the present invention is configured to include an optical system for improving human visual acuity including a high-number phase compensation element and a light amplitude correction element, the light amplitude correction element provides a calibration for monochromatic aberration. During use, the high-term phase compensating element can be expected to provide the effect of providing a high-term monochromatic calibration.

[Brief description of drawings]

FIG. 1 is a schematic diagram of an optical system adaptable to wavefront measurement, aberration correction, psychophysical measurement, and retinal image according to the present invention.

FIG. 2 is a schematic diagram of an optical system adaptable to wavefront measurement, aberration correction, psychophysical measurement, and retinal image according to the present invention.

[Figure 3]   FIG. 3 is a schematic view of an upper surface of an optical system according to an embodiment of the present invention.

FIG. 4 is a graph of amplitude transmission versus pupil radius for various values of σ (degree of apodization) for an apodization (optical image transmission control) filter according to one embodiment of the invention. .

FIG. 5 is a graph of amplitude transmission versus pupil radius under typical conditions for the Styles-Crawford model.

[Figure 6]   FIG. 6 is a graph of a spectral outline curve according to an embodiment of the present invention.

FIG. 7 is a graph of a spectral schematic curve according to an embodiment of the present invention,
It is about the wavelength function for different radial positions for each wavelength.

FIG. 8 is a light transmission curve for various pupil diameters according to one embodiment of the invention.

FIG. 9 is a diagram for an apodization filter according to an embodiment of the present invention.

FIG. 10 is a schematic diagram for an apodization filter according to another embodiment of the present invention.

FIG. 11 is a schematic diagram for an apodization filter according to one aspect of the present invention.

FIG. 12 is a transmission curve for an apodization filter according to an embodiment of the present invention.

FIG. 13 is a filter transmission curve of a long pass filter according to an embodiment of the present invention.

FIG. 14 is a graph of MTF showing the effect of different apodization filters according to embodiments of the present invention.

FIG. 15 is a graph of MTF showing the effect of different apodization filters according to embodiments of the present invention.

FIG. 16   FIG. 16 is a graph of MTF of different filters according to an embodiment of the present invention.

FIG. 17 is a graph of MTF with coma and spherical aberration calibrated by combining apodization filters according to an embodiment of the present invention.

FIG. 18 is a graph of monochromatic defocus as a function of wavelength tuned centered at a reference wavelength of 555 nm.

19 (a) and 19 (b) are graphs of contrast sensitivity against spatial frequency when the aberration is absent / present.

20 (a) and 20 (b) are graphs of the visual acuity advantage with respect to the spatial frequency before and after the aberration calibration according to the embodiment of the present invention.

FIG. 21 is a graph of contrast sensitivity and visual acuity benefits, respectively, for a 3 mm pupil radius for various aberration calibrations according to embodiments of the present invention.

FIG. 22 is a graph of contrast sensitivity and visual acuity benefits, respectively, for a 3 mm pupil radius for various aberration calibrations according to embodiments of the present invention.

FIG. 23 is a graph of visual acuity for several subjects, for different aberration calibrations, at different emission levels for a pupil diameter of 6 mm.

FIG. 24 is a graph of visual acuity for several subjects, for different aberration calibrations, at different emission levels for a pupil diameter of 6 mm.

FIG. 25 is a graph of visual benefit for different spatial frequencies as a function of wavelength bandwidth.

26 (a) and 26 (b) are graphs of MTF and visual benefit as a function of spatial frequency from 17 subjects at a pupil diameter of 3 nm, and FIGS. 26 (d) is a graph corresponding to a pupil diameter of 6 mm.

FIG. 27 is a graph of MTF as a function of spatial frequency for a neutral threshold curve illustrating the theoretical increase in visual acuity according to an embodiment of the invention.

[Explanation of symbols]

  118 distortion mirror   10, 190 Optical system   106 light emitting diode   110 beam splitter   125 transmission mirror   126 lenslet array   130 Heart Shack Wavefront Sensor   132 computer   134 Feedback control loop   136 interference filter   138 CRT   152 Lens manufacturing system (laser surgery platform)   155 optical path   156 Second CCD camera (retinal image CCD)   200 contact lenses   300 Broadband light source

─────────────────────────────────────────────────── ─── Continued front page    (81) Designated countries EP (AT, BE, CH, CY, DE, DK, ES, FI, FR, GB, GR, IE, I T, LU, MC, NL, PT, SE, TR), OA (BF , BJ, CF, CG, CI, CM, GA, GN, GW, ML, MR, NE, SN, TD, TG), AP (GH, G M, KE, LS, MW, MZ, SD, SL, SZ, TZ , UG, ZW), EA (AM, AZ, BY, KG, KZ, MD, RU, TJ, TM), AE, AG, AL, AM, AT, AU, AZ, BA, BB, BG, BR, BY, B Z, CA, CH, CN, CR, CU, CZ, DE, DK , DM, DZ, EE, ES, FI, GB, GD, GE, GH, GM, HR, HU, ID, IL, IN, IS, J P, KE, KG, KP, KR, KZ, LC, LK, LR , LS, LT, LU, LV, MA, MD, MG, MK, MN, MW, MX, MZ, NO, NZ, PL, PT, R O, RU, SD, SE, SG, SI, SK, SL, TJ , TM, TR, TT, TZ, UA, UG, UZ, VN, YU, ZA, ZW (72) Inventor Girao Antonio             Roche, New York, United States             Star Quinn Bee Road 280 F-term (reference) 2H006 BC02 BC06 BC07 BE05

Claims (68)

[Claims] 1. A process for calibrating (correcting) a monochromatic aberration with a high number of eyes for human vision, a process for calibrating a chromatic aberration with a high number of eyes for human vision, including: How to improve. 2. The method for improving human visual acuity according to claim 1, wherein the process of calibrating the monochromatic aberration with a high number of terms of the eye is a radial Zeniq mode with a number of terms higher than the third. 3. A process for calibrating a monochromatic wave aberration with a high number of terms of the eye is performed from the fifth to the first.
The method for improving human visual acuity according to claim 2, wherein the method is the 0th high-numbered radial Zenic mode. 4. The method for improving human visual acuity of claim 1, further comprising the step of calibrating defocus and astigmatism for human visual acuity. 5. The method of calibrating monochromatic aberrations with a high number of terms in the eye includes the step of measuring the wave aberration of the eye represented by the radial Zenic mode with a number higher than the third term. How to improve a person's eyesight. 6. The process of calibrating monochromatic aberration with a high number of terms in the eye starts from the fifth
The method for improving human visual acuity according to claim 1, comprising the step of measuring the wave aberration of the eye represented by the second highest number of radial Zenic modes. 7. The method of calibrating monochromatic aberrations with a high number of eyes of an eye comprises the step of providing an ophthalmic device with a step analysis diagram suitably adapted to calibrate said aberrations. How to improve a person's eyesight. 8. The method for improving visual acuity of a human according to claim 7, wherein the ophthalmic device comprises at least one of at least one contact lens, intraocular lens, ophthalmic inlay and ophthalmic onlay. 9. The step of calibrating a monochromatic aberration with a high number of eyes is a step of surgically modifying a characteristic of a human eye to calibrate a monochromatic aberration with a high number of eyes. Item 1. A method for improving the visual acuity of a person according to Item 1. 10. The step of the process of calibrating the chromatic aberration of the eye comprises the process of reducing the bandwidth of the spectrum (afterimage) of the incidental condition of visible light on the human eye, said bandwidth being from approximately 10 nm. The method for improving human visual acuity according to claim 1, which is in the range of 150 nm beyond the visible spectrum. 11. The human visual acuity improvement of claim 10, wherein the step of calibrating eye chromatic aberration further comprises the step of providing a bandpass filter to calibrate the eye chromatic aberration. Method. 12. The human visual acuity improvement of claim 10, wherein the step of calibrating the chromatic aberration of the eye further comprises the step of providing a pass filter that passes a long wavelength to calibrate the chromatic aberration of the eye. how to. 13. The method for improving human visual acuity according to claim 1, wherein the process of calibrating eye chromatic aberration includes a process of apodizing (optical image transmission control) a human pupil. 14. The process of apodizing the pupil (optical image transmission control) supplies non-uniform (constant) light amplitude transmission between the edge (edge portion) and the center of the pupil. A method for improving the visual acuity of a person according to claim 13. 15. The method for improving visual acuity of a human according to claim 14, wherein the transmission of light is increased from the edge of the pupil toward the center. 16. The method for improving human visual acuity of claim 14, wherein the process of apodizing the pupil is a function of wavelength. 17. Further, an apodization for calibrating the aberration (
11. The method for improving human visual acuity according to claim 10, further comprising a filter for controlling optical image transmission. 18. The human visual acuity improvement of claim 17, wherein the apodizing filter provides non-uniform (constant) non-uniform amplitude transmission of light across the pupil. Method. 19. The method for improving visual acuity of a human according to claim 18, wherein the amplitude transmission increases from the edge of the pupil toward the center. 20. The method for improving visual acuity of a human according to claim 1, wherein the correction of the chromatic aberration of the eye is to collectively supply a high number of monochromatic aberrations of the eye. 21. The method of improving visual acuity of a human according to claim 1, wherein the correction of the chromatic aberration of the eye supplies externally a high number of monochromatic aberrations of the eye. 22. An optical element selected from at least one of a contact lens, an intraocular lens, an inlay and an onlay, said element calibrating the wave aberration of the human eye with a high number of eyes. An ophthalmic device for improving the visual acuity of a person, the device having a surface shape adapted to, wherein the element is adapted to calibrate chromatic aberration. 23. The ophthalmic device for improving human vision according to claim 22, wherein the correction of the wave aberrations of the high-number monochromatic eye is a radial Zenic mode higher than the third number. 24. Correction of the wave aberrations of the high-number monochromatic eye is from the fifth to the first.
24. The ophthalmic device for improving human vision of claim 23, including a 0th state radial Zernic mode. 25. The ophthalmic device for improving human vision according to claim 22, wherein the element adapted to calibrate the chromatic aberration is an optical filter. 26. The ophthalmic device for improving human vision according to claim 25, wherein the optical filter is a neutral intensity (density) filter. 27. The optical filter is a bandpass filter.
An eye device for improving the visual acuity of the person described. 28. The optical filter is a long pass filter.
An eye device for improving the visual acuity of the person described. 29. The eye device for improving human vision according to claim 25, wherein the optical filter is an apodization (optical image transmission control) filter. 30. The apodization (optical image transmission control) filter,
30. The eye device for improving human visual acuity according to claim 29, wherein non-uniform (constant) amplitude amplitude transmission of light is performed between a rim (edge portion) and a center of the pupil. 31. The ophthalmic device for improving human vision according to claim 29, wherein the amplitude transmission is reduced from the center of the pupil to an edge. 32. The apodization (optical image transmission control) filter,
31. An ophthalmic device for improving human vision according to claim 30, which is spectrally dependent and provides a non-constant amplitude transmission of light between the edge and center of the pupil. 33. The ophthalmic device for improving human vision according to claim 32, wherein the attenuation of light from the center of the pupil to the edge portion is increased by the wavelength away from the reference wavelength. 34. The apodization (optical image transmission control) filter,
The eye device for improving human visual acuity according to claim 29, which is represented by a more than ordinary (transcendental) Gaussian function of an expression form of A (r) = exp (-r ⁴ / 2σ ² ). 35. The apodization (optical image transmission control) filter,
30. The ophthalmic device for improving human visual acuity according to claim 29, comprising an annular color-absorbing material of increasing intensity (density) from the center of the pupil to the edges. 36. The apodization (optical image transmission control) filter,
36. The ophthalmic device for improving human visual acuity of claim 35, which is in the band of approximately 500 nm to 650 nm in total. 37. The apodization (optical image transmission control) filter,
30. Improving human vision according to claim 29, comprising a plurality of adjacent annularly shaped filters, each annular filter being defined by a bandpass having a narrower bandwidth than an adjacent small annulus. Eye device. 38. The apodization (optical image transmission control) filter,
30. The person of claim 29, comprising a ring that is impermeable to light and has an inner diameter and a pass width having a bandwidth of between about 550 nm and 610 nm between the inner diameter and the outer diameter. Device that improves the eyesight of humans. 39. The ophthalmic device for improving vision of a human according to claim 38, wherein the inner radius is less than or equal to 2 mm. 40. The apodization (optical image transmission control) filter,
A plurality of adjacent annularly shaped filters, the filters providing a first annular ring impervious to the central radial portion of the element and providing a long pass filter that is adjacent to and larger than the first annular ring. 30. The ophthalmic device for improving human vision of claim 29, wherein the second annular ring provides a bandpass filter. 41. The ophthalmic device for improving human visual acuity of claim 40, wherein the long-pass filter transmits wavelengths greater than approximately 510 nm and the bandpass filter performs transmission between approximately 550 nm and 610 nm. 42. The apodization (optical image transmission control) filter,
30. The ophthalmic device for improving human vision of claim 29, comprising a long pass filter. 43. The ophthalmic device for improving human vision of claim 42, wherein the long pass filter transmits wavelengths above a reference wavelength of substantially approximately 555 nm. 44. A phase compensation element (means) having a high number of terms,   An optical system for improving a person's visual acuity, which includes a light amplitude correcting element (means). 45. The optical system for improving human visual acuity according to claim 44, wherein the high-number phase compensation means and the light amplitude correction means are common optical components present. 46. The optical system system for improving human visual acuity according to claim 44, wherein the high number phase compensating means and the light amplitude changing means are optical components respectively provided separately. 47. An optical system for improving human vision according to claim 44, wherein the high-term phase compensating means is a distorted (deformed) mirror. 48. The optical system for improving human visual acuity according to claim 44, wherein the high-number phase compensator is a liquid crystal device. 49. The optical system for improving human vision according to claim 44, wherein the high-number phase compensator is a contact lens. 50. The high-term phase compensating means is an intraocular lens.
An optical system for improving the visual acuity of the described person. 51. The optical system for improving human visual acuity according to claim 44, wherein the high-number phase compensation means is a reshaped (recreated) cornea. 52. The high-term phase compensating means is an ophthalmic inlay.
4. An optical system system for improving human vision as described in 4. 53. The ophthalmological onlay is used as the phase compensation means having a high number of terms.
4. An optical system system for improving human vision as described in 4. 54. The optical system according to claim 44, wherein the light amplitude changing means is a filter. 55. The optical system of claim 54, wherein the filters are filters with at least one passband and longpass filters. 56. The optical system system for improving human visual acuity according to claim 44, wherein the light amplitude changing means is a pupil of a person subjected to apodization (optical image transmission control). 57. The pupil subjected to the apodization (optical image transmission control) supplies non-uniform amplitude transmission of light between the edge (edge portion) and the center of the pupil. Item 56. An optical system for improving human vision according to Item 56. 58. The pupil subjected to the apodization (optical image transmission control) is spectrally dependent and performs non-constant light amplitude transmission between the edge (edge portion) and the center of the pupil. 57. An optical system for improving human vision according to claim 56. 59. The general optical component comprises at least one contact lens,
47. An optical system for improving human vision according to claim 45, comprising an intraocular lens, an inlay, and an onlay. 60. The phase compensating means is at least one contact lens, an intraocular lens, an inlay, and an onlay, and a reformed (recreated) cornea present, and the optical amplitude changing means is present at least one. 47. An optical system for improving human vision according to claim 46, which is one contact lens, an intraocular lens, an inlay, an onlay, and an external optical component for use with a phase compensation means. 61. An optical system system for improving human visual acuity according to claim 44, wherein the phase compensating means and the optical amplitude correcting means are arranged on an optical axis of the optical system. 62. The method of improving visual acuity of a person of claim 1, further comprising the step of measuring monochromatic aberrations and chromatic aberrations of the eye with a high number of at least one eye. 63. Generating means for generating a reflection point source image of the retina of a living eye; receiving means for receiving the reflection point source image; and converting the point source image into a corresponding digital signal. Converting means, calculating means for calculating a high number of monochromatic aberrations using the digital signal, and a disk (surface) of the retina of the living eye for generating a disk (surface) image of the retina. Illuminating means for illuminating, the high-number phase-compensating optical element in the optical path of the system is adjusted to calibrate the high-number monochromatic aberrations, and the optical amplitude changing element is Providing means for providing an image of the disc (surface) of the reflected retina after calibration of high-number monochromatic and chromatic aberrations, arranged in the optical path of the system for calibrating chromatic aberrations; Prepared alive Optics system for generating a high resolution image of the retina. 64. The optical system of claim 63, wherein the high number phase compensating optical element is one of a distorted mirror, a liquid crystal device, and a MEMS device. 65. The optical system of claim 62, wherein the optical amplitude modifying element is one of an artificial apodization (optical image transmission control) element and an optical filter. 66. Generating a reflection point source image of the retina of a living eye, converting the point source image into a corresponding digital signal, and using the digital signal to generate a high number of monochromatic aberrations. Calculating, illuminating the surface of the retina of the living eye to create a retina disc (surface) image, and shutting off the retina disc (surface) image with a high number of phase-compensating optics The phase compensating optical element is provided such that the wavefront compensation for the wave aberration is adjusted so that it is provided for the living eye, and the optical amplitude correction means for calibrating the chromatic aberration is provided. A method of producing a high resolution image of the retina of a living eye including the steps. 67. The method of producing a high resolution image of a living retina according to claim 66, wherein illuminating the surface of the retina is with a broadband light source. 68. The high resolution image of the retina of a living eye of claim 66, wherein the step of correcting chromatic aberration is an artificial apodization (optical image transmission control) pupil of the optical system. how to.